WO2020139306A1 - Method of computed tomography - Google Patents
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- WO2020139306A1 WO2020139306A1 PCT/UA2019/000042 UA2019000042W WO2020139306A1 WO 2020139306 A1 WO2020139306 A1 WO 2020139306A1 UA 2019000042 W UA2019000042 W UA 2019000042W WO 2020139306 A1 WO2020139306 A1 WO 2020139306A1
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- 238000002591 computed tomography Methods 0.000 title claims abstract description 16
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- 208000001871 Tachycardia Diseases 0.000 description 4
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/48—Diagnostic techniques
- A61B6/486—Diagnostic techniques involving generating temporal series of image data
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
- A61B6/4233—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
- A61B6/5264—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to motion
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/58—Testing, adjusting or calibrating thereof
- A61B6/582—Calibration
- A61B6/585—Calibration of detector units
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
- G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
- G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
- G01N23/046—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material using tomography, e.g. computed tomography [CT]
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- G—PHYSICS
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- G06T11/008—Specific post-processing after tomographic reconstruction, e.g. voxelisation, metal artifact correction
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/025—Tomosynthesis
Definitions
- This invention relates to the method of computed tomography on the basis of stored roentgenological images series that had been formed during short (usually from 2 to 16 s) periods by any tomographs having high-speed flat multisensor digital X-ray receivers based on optoelectronic converters with partial overlapping visual fields of theirs.
- Such method is meant preferably for diagnostics of movable viscera (especially a heart against tachycardia, aperiodic arrhythmia and tachyarrhythmia) and rapid physiological processes (such as local bloodstream within a brain and extremities’ parts), and for examination of patients suffering from involuntary convulsive activity.
- X-ray units i.e. between an X-ray emitter and a digital X-ray receiver
- cone-beam computer tomographs each of which has a rotational annular support of oppositely fixed a controllable X-ray emitter and an X-ray receiver
- a controllable X-ray emitter and an X-ray receiver
- Cone-beam computed tomography a new low dose, high resolution imaging technique of the wrist, presentation of three cases with technique // Skeletal Radiology. 2012. Ns 41. V.1 , pp. 93-96; 2. Ramdhian-Wihlm R., Le Minor J.
- Free distances between X-ray units within aforesaid annular supports are small and can only sometimes insignificantly exceed average size of adults’ head. It is comfortable for tomography of cartilages and bones of hands and feet, cubital, knee and talocrural joints and brainpans, but is unsuitable for transmission scanning of chest viscera in principle.
- Placement of a torso (and even a patient in whole for X-ray scanning various body parts) is possible by use of tomographs equipped with horizontal roentgenoparent tables.
- spiral tomographs which have annular supports’ bore 78 cm, length of a spiral row of X-ray sensors 100 cm that confines tomography area having diameter up to 60 cm, and up to 64 and more of such rows (see e.g., RAD BOOK 2015. The Radiology Guide to Technology and Information in Europe, section“Computer Tomography”, pp. 9-12, especially p. 12). This allows synthesizing adequate number tomograms during one diagnostic session that goes, as a rule, about several tens of seconds.
- All such supports are low-inertia in comparison with aforesaid heavy annular supports of spiral tomographs and can start-stop operate.
- the slit X-ray emitter can pulse that decreases radiation exposure of patients. However even continuous operations of this emitter during diagnostic session no induce overradiation because pyramidal X-ray beam moves within narrow sector (as a rule, ⁇ 20°), its angular velocity is low, and duration of diagnostic studies is usually no more than 6 second.
- Such computer tomographs can be equipped with multisensor digital X-ray receivers based on optoelectronic converters with partial overlapping visual fields of theirs. Principle of operation of such receivers was disclosed in the patents UA 22127 and RU 2127961 on the basis of PCT/UA 96/00016 (WO 98/11722).
- a process includes following steps:
- This processing includes traditionally -
- these documents disclose a linear pyramidal-beam X-ray tomograph having C-like support of X-ray units and a resettable roentgenoparent table. This enables X- ray transmission scanning in the angular range ⁇ 45°, if the table is located perpendicularly to geometrical axis of a horizontal shaft of the C-like support, and even up to ⁇ 1 10°, if the table is located along this geometrical axis.
- This known method includes: (1 ) Placement of a selected patient’s body part opposite a multisensor digital X-ray receiver based on a set of optoelectronic converters having partially overlapped visual fields;
- All steps (1) - (8) of this method perform on a real-time basis that is enough for obtainment of qualitative tomograms of immovable or low-mobile organs.
- fragmentary analogous video signals having duration about 30 milliseconds are smeared, if they obtained by X-ray transmission scanning of a pulsed heart (especially against tachycardia, aperiodic arrhythmia and tachyarrhythmia), rapid physiological processes such as local bloodstream, and patients suffering from involuntary convulsive activity. This worsens observability of anatomical and/or physiological anomalies substantially and complicates (and sometimes excludes) correct diagnosis.
- CMOS-devices are known at present as optoelectronic converters. They are capable to generate output streams of video information at average intensity no less than 130 megapixels per second. It is known also that generation of one integral output digital video signal for the purpose of tomography is possible as a result of synchronous work of at least 100 identical optoelectronic converters. Therefore intensity of output video data stream generated by CMOS-sensors set makes up about 13 gigapixels per second. This quantity exceeds manifold PCs-interfaces throughput that no exceeds 300 megapixel per second if even their clock frequency comes up to 10 GHz.
- the invention is based on the problem - by way of improvement of performance - to create method of computed tomography that prevents smearing of roentgenological images in time of diagnosing of movable organs and rapid physiological processes.
- Said discrete detection of light stream and conversion of light beams into fragmentary analogous video signals execute by optoelectronic converters having working frequency no less than 250 fps;
- Said fragmentary digital video signals record serially into a video buffer and delay in this video buffer till completion of said X-ray transmission scanning, and
- the proposed method separates process of generation initial video data from process of their conversion into tomograms. Under such conditions generation of fragmentary digital video signals and their buffering at rate no less than 250 fps before transmission to tomosynthesis allow:
- First additional feature consists in that the X-ray transmission scanning of a selected patient’s body part within specified angular range realizes by linear movement and concomitant angular displacement of the rotary X-ray emitter having rectangular collimator along frontal surface of immobile X-ray receiver. This allows accomplishment of the proposed method using slightly improved non-expensive and easy-to-use ordinary basic radiography systems, which are widespread in medical institutions including many stationary and movable outpatient clinics.
- Second additional feature consists in that said X-ray transmission scanning of a selected patient’s body part realizes within angular range ⁇ 20°. This is usually enough for true diagnosis of any pulsed heart.
- Third additional feature consists in that the X-ray transmission scanning of a selected patient’s body part within specified angular range realizes by synchronous angular movement of oppositely fixed said X-ray receiver and said X-ray emitter having the rectangular collimator. This allows accomplishment of the proposed method using presented in many clinics pyramidal-beam computer tomographs equipped with C-like supports of X-ray units and drives of swinging motion of theirs.
- Fourth additional to the third feature consists in that said X-ray transmission scanning of a selected patient’s body part realizes within angular range ⁇ 1 10° This allows examination of beast farming animals (e.g. sires, studs, work and athletic horses etc.).
- beast farming animals e.g. sires, studs, work and athletic horses etc.
- Fig. 1 shows a skeleton diagram of such video path of a computer tomograph, which is minimally required for realization of the proposed method
- Fig. 2 shows an advanced single-column basic system of computed tomography (characterized by horizontal initial location of C-like support of the X-ray units);
- Fig. 3 shows the same that Fig. 2 (but characterized by vertical initial location of C-like support of the X-ray units).
- the proposed method can be realized using any computer tomograph, a video path of which has at least (see Fig. 1):
- a flat multisensor digital X-ray receiver 2 comprising serially arranged along ray course:
- a set of optoelectronic converters 4 characterized by partial overlapping of their visual fields, which are fixed within openings of a non-transparent to residual X-ray irradiation panel 5, and which are chosen as produced by SONY CMOS-sensors IMX287LLR that meet the standard 1/3 inch and capable to generate fragmentary analogous video signals sized as 728(H) x 544(V) at working frequency 330 fps and duration of each single video signal about 3 msec (www.sony.net/cis-industry),
- ADCs analog-digital converters
- Buffer video memory cells 8 (particularly, GDDR5 type), which are connected with said microprocessors 7 by lines that able operate in feedforward and feedback modes;
- PC personal computer
- Programmable microprocessors 7 can be mounted as 32-digit gate arrays Nios II produced by Altera (https://www.altera.com/products/processors/support.html). These arrays have internal timers that can adjust to various working frequency, memory controllers and own interfaces.
- Memory controllers of the microprocessors 7 are meant to form commands to record frames (that is fragmentary digital video signals generated by ADCs 6 with a glance of actual working frequency of the optoelectronic converters 4), and commands to their transmission for following treatment. Respectively, the interfaces of these microprocessors 7 must be adjusted in two ways -
- a computer tomograph for realization of the proposed method can be produced, e.g., on the basis of a single-column digital roentgenological system UNIMAT DRad of the firm X ray Swiss (http://www.xray-swiss.ch).
- First carriage 12 that has mounted onto above-mentioned ways in the pillar 1 1 and is able to controllable vertical reciprocal motion and to arrest at specified level;
- this C-like support mounted on said carriage 12 a C-like support that can turn to the left or right relative to horizontal axis; this C-like support composed of a transverse 13 having not designated especially radially oriented ways and opposite horizontal cantilever bars 14 positioned onto these ways with possibility of synchronous adjusting approach or moving away.
- One in two cantilever bars 14 serves as guide bearing for reciprocally movable controllable second carriage 15 that carries a rotary X-ray emitter 1 having the rectangular collimator, whereas other cantilever bar 14 serves as simple support of rigidly fixed said multisensor digital X-ray receiver 2.
- this tomograph can be equipped with a not showed especially gurney having roentgenoparent table.
- the proposed method includes three stages.
- First (preparatory) stage includes such steps:
- Second basic stage which must be realized on a real-time basis, includes:
- This stage must be executed after completion of X-ray transmission scanning according to actual engineering factors and software of the PC 10. This stage includes:
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Abstract
Method of computed tomography includes X-ray transmission scanning of a selected body part within specified angular range, conversion of X-rays transmitted under various angles through said body part into visible light stream; discrete detection of it by optoelectronic converters having characteristic working frequency no less than 250 fps, conversion of light beams into fragmentary analogous video signals; analog-digital conversion of theirs into fragmentary digital video signals, their record serially into a video buffer and delay in this video buffer till completion of said X-ray transmission scanning, and then execute correction of luminance and geometrical defects of fragmentary digital video signals, conjunction of corrected fragmentary digital video signals into integral digital video signals and computer tomosynthesis. Such method allows to eliminate smearing of tomograms and to increase quality of diagnostics of pulsatory heart and rapid physiological processes.
Description
METHOD OF COMPUTED TOMOGRAPHY
Field of the Invention
This invention relates to the method of computed tomography on the basis of stored roentgenological images series that had been formed during short (usually from 2 to 16 s) periods by any tomographs having high-speed flat multisensor digital X-ray receivers based on optoelectronic converters with partial overlapping visual fields of theirs.
Such method is meant preferably for diagnostics of movable viscera (especially a heart against tachycardia, aperiodic arrhythmia and tachyarrhythmia) and rapid physiological processes (such as local bloodstream within a brain and extremities’ parts), and for examination of patients suffering from involuntary convulsive activity.
Background Art
Now computed tomography is well known as method of differential diagnostics of diseases and traumata of human and animal viscera (see, e.g., Suetens P. Fundamentals of medical imaging. - Cambridge University Press, 2nd ed., 201 1 ). It includes -
Placement of any body part of a patient (notably a human or an animal) between X-ray units (i.e. between an X-ray emitter and a digital X-ray receiver);
X-ray transmission scanning of the selected patient’s body part when at least X-ray emitter moves along a predetermined trajectory relative to the said body part,
Reception of X-ray radiation that had transmitted through each regular slice of the selected patient’s body part and its conversion into visible light beams,
Following conversion of the visible light beams into electrical signals, analog-digital conversion of these signals into digital video data and generation of each regular digital roentgenological image of oblique view of the selected patient’s body part, and
A computer tomosynthesis on the basis of the roentgenological images series.
Typical software for computed tomography is available, as a rule, at the market (see, for example, US 2008/0219567 A1 ). Development of executives for mechanical and electrical units of tomographs is easily too. Therefore many computer tomographs having various purpose and design have already developed and are operating.
However, such problem as X-ray transmission scanning of pulsed hearts, some blood- vascular system parts characterized by rapid bloodstream, and patients suffering from involuntary convulsive activity is not solved until now.
For instance, such so called cone-beam computer tomographs are known, each of which has a rotational annular support of oppositely fixed a controllable X-ray emitter and an X-ray receiver [see, for example: 1. De Cock J., Mermuys K., Goubau J., Van Petegem S., Houthoofd B., Casselman J.W. Cone-beam computed tomography: a new low dose, high resolution imaging technique of the wrist, presentation of three cases with technique // Skeletal Radiology. 2012. Ns 41. V.1 , pp. 93-96; 2. Ramdhian-Wihlm R., Le Minor J. M., Schmittbuhl M., Jeantroux J., Mac Mahon P., Veillon F., Dosch J.-C., Dietemann J.-L, Bierry G. Cone-beam computed tomography arthrography: an innovative modality for the
evaluation of wrist ligament and cartilage injuries // Skeletal Radiology. 2012. V. 41. pp. 936-969; 3. A.KD. BacwibeB, H.H. EPMHOB (MP,), E.A. Eropoea. KoHycHO-nyneBafl KOMnbfOTepHaa TOMorpacfMfl - Hoeaa TQCHOPOGMA uccneflOBaHUH B TRQBMQTOPOGMM // MEflMMI/IHCKAR BM3UA/1M3AI_1MA. N°4 2012, c. 65-68 (In English: A.Yu. Vasil'ev, N.N. Blinov (Jr.), E.A. Egorova. Cone-beam Computer Tomography - New Technology of Research in Traumatology // MEDICAL IMAGING. N°4, 2012, pp. 65-68), and many other].
Free distances between X-ray units within aforesaid annular supports are small and can only sometimes insignificantly exceed average size of adults’ head. It is comfortable for tomography of cartilages and bones of hands and feet, cubital, knee and talocrural joints and brainpans, but is unsuitable for transmission scanning of chest viscera in principle.
Placement of a torso (and even a patient in whole for X-ray scanning various body parts) is possible by use of tomographs equipped with horizontal roentgenoparent tables.
At present two types of such tomographs are known.
Big specialized clinics have usually computer tomographs equipped with great annular supports of X-ray units, notably a controllable X-ray emitter having a slit collimator for shaping of fan-like X-ray beam and a multisensor digital X-ray receiver (see e.g., US 6,574,296). Each such support has a drive of continual rotation around a roentgenoparent table, which is by-turn equipped with a drive of reciprocal motion along geometrical axis of said annular support.
Rotation of this support at rate 2 - 4 rps around the table and synchronous linear movement of this table along geometrical axis of said support enable spiral movement of fan-like X-ray beam relative to a patient’s body.
Now such spiral tomographs are known, which have annular supports’ bore 78 cm, length of a spiral row of X-ray sensors 100 cm that confines tomography area having diameter up to 60 cm, and up to 64 and more of such rows (see e.g., RAD BOOK 2015. The Radiology Guide to Technology and Information in Europe, section“Computer Tomography”, pp. 9-12, especially p. 12). This allows synthesizing adequate number tomograms during one diagnostic session that goes, as a rule, about several tens of seconds.
Unfortunately these tomographs are very complicate structurally and bulky, and therefore effortful in production and service. In fact, their annular supports together with X- ray units are massive and cannot start-stop operate. Thus the X-ray emitter must operate continuously during each diagnostic session.
Municipal hospitals have usually relatively low-price and easy-to-use computer tomographs, in which X-ray units are oppositely arranged onto parallel horizontal cantilever bars of C-like supports [see, for example, yMe6Hoe noco6we «KoivmbiOTepHafl ToMorpacjjMH» on website <http://www. radioland.net.ua/contentid-1 12-page1 .html>, pnc. 1.1 (In English a handbook“Computed Tomography”, Fig. 1.1 )]. Each such support has drive of swinging motion relative to an immobile roentgenoparent table within defined angular range. All such supports are low-inertia in comparison with aforesaid heavy annular
supports of spiral tomographs and can start-stop operate. The slit X-ray emitter can pulse that decreases radiation exposure of patients. However even continuous operations of this emitter during diagnostic session no induce overradiation because pyramidal X-ray beam moves within narrow sector (as a rule, ± 20°), its angular velocity is low, and duration of diagnostic studies is usually no more than 6 second.
Such computer tomographs can be equipped with multisensor digital X-ray receivers based on optoelectronic converters with partial overlapping visual fields of theirs. Principle of operation of such receivers was disclosed in the patents UA 22127 and RU 2127961 on the basis of PCT/UA 96/00016 (WO 98/11722). A process includes following steps:
(1 ) Conversion of X-ray radiation that had transmitted through a selected patient’s body part into visible light stream,
(2) Discrete detection of this light stream by many optoelectronic converters having partially overlapped visual fields, and conversion of obtained light beams into fragmentary analogous video signals,
(3) Conversion of fragmentary analogous video signals into fragmentary digital video signals that go into subsequent processing.
This processing includes traditionally -
(4) Correction of luminance and such geometrical defects of fragmentary digital video signals that caused by sizing and mounting errors of the optoelectronic converters and by partial overlapping visual fields of theirs, and
(5) Conjunction of each regular set of corrected fragmentary digital video signals into an integral output digital video signal that gives either a single roentgenogram, which can be recorded for following reproduction and analysis, or any part of roentgenological images series for following computed tomography.
All above-mentioned steps (1 ) - (5) perform on a real-time basis.
Initially matrixes composed of TV-cameras and later diode target arrays were used (and use at present) as sets of optoelectronic converters. They have working frequency no more than 30 fps.
Moreover, use of the same optoelectronic converters was specified in multisensor digital X-ray receivers in the form of joined at obtuse angle at least two flat receivers’ sections (see WO/2017/200507 and UA 1 17599 on the basis of PCT/UA 2016/000065).
In addition, these documents disclose a linear pyramidal-beam X-ray tomograph having C-like support of X-ray units and a resettable roentgenoparent table. This enables X- ray transmission scanning in the angular range ± 45°, if the table is located perpendicularly to geometrical axis of a horizontal shaft of the C-like support, and even up to ± 1 10°, if the table is located along this geometrical axis.
Functional analysis of structure and specification of operation of said tomograph allow disclosing a method of computed tomography, subject matter of which is the closest to the proposed further method. This known method includes:
(1 ) Placement of a selected patient’s body part opposite a multisensor digital X-ray receiver based on a set of optoelectronic converters having partially overlapped visual fields;
(2) X-ray transmission scanning of the selected patient’s body part within specified angular range by an X-ray emitter having a rectangular collimator;
(3) Conversion of X-ray radiation that had transmitted at various angles through the selected patient’s body part into visible light stream;
(4) Discrete detection of this light stream by many optoelectronic converters having partially overlapped visual fields (namely TV-cameras, or diode target arrays having characteristic working frequency about 30 fps), and conversion of obtained light beams into fragmentary analogous video signals,
(5) Conversion of fragmentary analogous video signals into fragmentary digital video signals;
(6) Correction of luminance and such geometrical defects of fragmentary digital video signals that caused by sizing and mounting errors of the optoelectronic converters and by partial overlapping visual fields of theirs;
(7) Conjunction of corrected fragmentary digital video signals into integral digital video signals corresponding to the roentgenological images of oblique projections of the patient’s body part; and
(8) Computer tomosynthesis on the basis of the roentgenological images series.
All steps (1) - (8) of this method perform on a real-time basis that is enough for obtainment of qualitative tomograms of immovable or low-mobile organs.
However, it was found that fragmentary analogous video signals having duration about 30 milliseconds (and further respective roentgenological images) are smeared, if they obtained by X-ray transmission scanning of a pulsed heart (especially against tachycardia, aperiodic arrhythmia and tachyarrhythmia), rapid physiological processes such as local bloodstream, and patients suffering from involuntary convulsive activity. This worsens observability of anatomical and/or physiological anomalies substantially and complicates (and sometimes excludes) correct diagnosis.
It can seem that this disadvantage can easily eliminate by use of modern optoelectronic converters having work frequency 250 and more fps and duration of each single video signal less than 4 msec (www.sony.net/cis-industry).
Unfortunately, other boundary conditions come into force in this case.
So, CMOS-devices are known at present as optoelectronic converters. They are capable to generate output streams of video information at average intensity no less than 130 megapixels per second. It is known also that generation of one integral output digital video signal for the purpose of tomography is possible as a result of synchronous work of at least 100 identical optoelectronic converters. Therefore intensity of output video data stream generated by CMOS-sensors set makes up about 13 gigapixels per second. This quantity exceeds manifold PCs-interfaces throughput that no exceeds 300 megapixel per second if
even their clock frequency comes up to 10 GHz.
Summary of the Invention
The invention is based on the problem - by way of improvement of performance - to create method of computed tomography that prevents smearing of roentgenological images in time of diagnosing of movable organs and rapid physiological processes.
This problem has solved in that in a method of computed tomography that includes following steps:
(1 ) Placement of a patient’s body part opposite a multisensor digital X-ray receiver based on a set of optoelectronic converters having partially overlapped visual fields;
(2) X-ray transmission scanning of the selected patient’s body part within specified angular range by an X-ray emitter having a rectangular collimator;
(3) Conversion of X-ray radiation that had transmitted at various angles through the selected patient’s body part into visible light stream;
(4) Discrete detection of this light stream by many optoelectronic converters having characteristic working frequency, and conversion of obtained light beams into fragmentary analogous video signals,
(5) Conversion of said analogous video signals into fragmentary digital video signals;
(6) Correction of luminance and such geometrical defects of fragmentary digital video signals that caused by sizing and mounting errors of the optoelectronic converters and by partial overlapping visual fields of theirs;
(7) Conjunction of corrected fragmentary digital video signals into integral digital video signals corresponding to the roentgenological images of oblique projections of the patient’s body part; and
(8) Computer tomosynthesis on the basis of the roentgenological images series.
According to the invention
Said discrete detection of light stream and conversion of light beams into fragmentary analogous video signals execute by optoelectronic converters having working frequency no less than 250 fps;
Said fragmentary digital video signals record serially into a video buffer and delay in this video buffer till completion of said X-ray transmission scanning, and
Only then execute correction of luminance and geometrical defects of fragmentary digital video signals, conjunction of corrected fragmentary digital video signals into integral digital video signals and computer tomosynthesis.
The proposed method separates process of generation initial video data from process of their conversion into tomograms. Under such conditions generation of fragmentary digital video signals and their buffering at rate no less than 250 fps before transmission to tomosynthesis allow:
Firstly, to increase sharply quality of diagnosis of blood-vascular system diseases as a result of separation rapid generation and recording of high-quality non-smeared initial
roentgenological images of oblique projections of pulsatory heart and/or pulse waves from relatively slowly following transformation of such images into tomograms,
Secondly, to minimize radiation exposure of patients as additional bonus.
First additional feature consists in that the X-ray transmission scanning of a selected patient’s body part within specified angular range realizes by linear movement and concomitant angular displacement of the rotary X-ray emitter having rectangular collimator along frontal surface of immobile X-ray receiver. This allows accomplishment of the proposed method using slightly improved non-expensive and easy-to-use ordinary basic radiography systems, which are widespread in medical institutions including many stationary and movable outpatient clinics.
Second additional feature consists in that said X-ray transmission scanning of a selected patient’s body part realizes within angular range ± 20°. This is usually enough for true diagnosis of any pulsed heart.
Third additional feature consists in that the X-ray transmission scanning of a selected patient’s body part within specified angular range realizes by synchronous angular movement of oppositely fixed said X-ray receiver and said X-ray emitter having the rectangular collimator. This allows accomplishment of the proposed method using presented in many clinics pyramidal-beam computer tomographs equipped with C-like supports of X-ray units and drives of swinging motion of theirs.
Fourth additional to the third feature consists in that said X-ray transmission scanning of a selected patient’s body part realizes within angular range ± 1 10° This allows examination of beast farming animals (e.g. sires, studs, work and athletic horses etc.).
Brief Description of the Drawings
The invention will now be explained by detailed description of proposed method of computed tomography on the basis of its hardware implementation with references to the accompanying drawings, in which:
Fig. 1 shows a skeleton diagram of such video path of a computer tomograph, which is minimally required for realization of the proposed method;
Fig. 2 shows an advanced single-column basic system of computed tomography (characterized by horizontal initial location of C-like support of the X-ray units);
Fig. 3 shows the same that Fig. 2 (but characterized by vertical initial location of C-like support of the X-ray units).
Best Embodiments of the Invention
The proposed method can be realized using any computer tomograph, a video path of which has at least (see Fig. 1):
An (preferably rotary) X-ray emitter 1 having a rectangular collimator;
A flat multisensor digital X-ray receiver 2 comprising serially arranged along ray course:
- a roentgenoparent frontal wall (that is not designated especially),
- a flat X-ray-to-optical converter 3,
- a set of optoelectronic converters 4 characterized by partial overlapping of their visual fields, which are fixed within openings of a non-transparent to residual X-ray irradiation panel 5, and which are chosen as produced by SONY CMOS-sensors IMX287LLR that meet the standard 1/3 inch and capable to generate fragmentary analogous video signals sized as 728(H) x 544(V) at working frequency 330 fps and duration of each single video signal about 3 msec (www.sony.net/cis-industry),
- analog-digital converters (ADCs) 6 mounted onto back side of the panel 5 and connected to the optoelectronic converters 4 outputs;
- programmable microprocessors 7, which mounted also onto back side of the panel
5, connected to the ADCs 6 outputs and meant for rapid transmission of fragmentary digital video signals to temporal recording and storage of these primary video data during X-ray scanning and to transmission of these video data to finishing treatment after completion of said scanning;
Buffer video memory cells 8 (particularly, GDDR5 type), which are connected with said microprocessors 7 by lines that able operate in feedforward and feedback modes;
Interface block 9 of said microprocessors 7 with such personal computer (PC) 10, which has software necessary for correction initial fragmentary digital video signals and conjunction of corrected fragmentary digital video signals into integral digital video signals corresponding to roentgenological images of single oblique projections, and for tomosynthesis.
Programmable microprocessors 7 can be mounted as 32-digit gate arrays Nios II produced by Altera (https://www.altera.com/products/processors/support.html). These arrays have internal timers that can adjust to various working frequency, memory controllers and own interfaces.
Memory controllers of the microprocessors 7 are meant to form commands to record frames (that is fragmentary digital video signals generated by ADCs 6 with a glance of actual working frequency of the optoelectronic converters 4), and commands to their transmission for following treatment. Respectively, the interfaces of these microprocessors 7 must be adjusted in two ways -
Only to record and delay of said frames into buffer video memory cells 8 in feedforward mode during each regular session of X-ray scanning, and
Only to playback of earlier recorded and delayed frames from said cells 8 in feedback mode and their transmission through interface block 9 into PC 10 after completion of said scanning.
A computer tomograph for realization of the proposed method can be produced, e.g., on the basis of a single-column digital roentgenological system UNIMAT DRad of the firm X ray Swiss (http://www.xray-swiss.ch).
Mechanical basis of such advanced tomograph has (see Figs 2 and 3):
A standard vertical pillar 1 1 having not designated especially longitudinal ways;
First carriage 12 that has mounted onto above-mentioned ways in the pillar 1 1 and is able to controllable vertical reciprocal motion and to arrest at specified level;
Mounted on said carriage 12 a C-like support that can turn to the left or right relative to horizontal axis; this C-like support composed of a transverse 13 having not designated especially radially oriented ways and opposite horizontal cantilever bars 14 positioned onto these ways with possibility of synchronous adjusting approach or moving away.
One in two cantilever bars 14 serves as guide bearing for reciprocally movable controllable second carriage 15 that carries a rotary X-ray emitter 1 having the rectangular collimator, whereas other cantilever bar 14 serves as simple support of rigidly fixed said multisensor digital X-ray receiver 2.
Additionally this tomograph can be equipped with a not showed especially gurney having roentgenoparent table.
The proposed method includes three stages.
First (preparatory) stage includes such steps:
(1 ) Arrangement of first carriage 12 (and, respectively, the C-like support of X-ray units) on specified level relative to the pillar 1 1 and arrest of it;
(2) Arrangement of the C-like support of the X-ray units 1 and 2 by angular displacement on 90° into one in a two initial configurations, namely:
(2.1 ) either into the configuration according to the Fig. 2, when both horizontal cantilever bars 14 are located on identical high level, said X-ray receiver 2 is arrested in the middle of one cantilever bar 14, and the second carriage 15 together with the rotary X-ray emitter 1 is putted into one in two end positions on the other cantilever bar 14 (it is convenient for patients’ examination in standing position);
(2.2) or into configuration according to the Fig. 3, when both horizontal cantilever bars
14 are located in one vertical plane and said X-ray receiver 2 and second carriage 15 together with said X-ray emitter 1 are fixed in the middle of respective cantilever bars 14 (it is necessary, when patients lies on a not shown here roentgenoparent table, which can be placed into the gap between the X-ray units 1 and 2);
(3) Additional adjustment of a gap between the X-ray emitter 1 and the X-ray receiver
2 by synchronous movement of cantilever bars 14 along above-mentioned ways of the transverse 13 (if such trimming is necessary);
(4) Placement of a patient within the gap between the X-ray units 1 and 2 (at that a vertically standing patient must lean to the receiver 2 roentgenoparent wall, whereas a lying patient must be fixed onto above-mentioned roentgenoparent table from casual displacement during X-ray scanning of the selected patient’s body part);
Second basic stage, which must be realized on a real-time basis, includes:
(5) switch of power of the X-ray emitter 1 having the rectangular collimator and continuous X-ray transmission scanning of selected patient’s body part within specified
angular range, notably -
(5.1 ) either preferably in the range ± 20° by linear movement of the X-ray emitter from one end of the cantilever bar 14 to other its end and by rotational displacement of pyramidal X-ray beam following said linear movement (see Fig. 2),
(5.2) or preferably in the range ± 1 10° by synchronous turn to the left or right of the transverse 13 and oppositely fixed the X-ray emitter 1 and the X-ray receiver 2 (see Fig. 3);
(6) Generation of continuous visible light stream by the X-ray-to-optical converter 3 as far as pyramidal X-ray beam transmits under various angles through the selected patient’s body part;
(7) Discrete detection of this light stream by optoelectronic converters 4 having characteristic working frequency (particularly no less than 250 fps) and conversion of obtained light beams into fragmentary analogous video signals;
(8) Conversion of fragmentary analogous video signals by ADCs 6 into fragmentary digital video signals;
(9) Consecutive writing of fragmentary digital video signals according to the commands of programmable microprocessors 7 into the buffer video memory cells 8 and delay of theirs in these cells 8 till completion of said X-ray transmission scanning of the selected patient’s body part.
Third basic stage must be executed after completion of X-ray transmission scanning according to actual engineering factors and software of the PC 10. This stage includes:
(10) Correction of luminance and such geometrical defects of fragmentary digital video signals that caused by sizing and mounting errors of the optoelectronic converters and by partial overlapping visual fields of theirs;
(11) Conjunction of corrected fragmentary digital video signals into integral digital video signals corresponding to the roentgenological images of oblique projections of patient’s body part; and
(12) Computer tomosynthesis on the basis of the roentgenological images series.
Industrial applicability
Industrial applicability of the invention has provided because all components necessary for realization of the proposed method are now individually available at the world market.
Claims
1. A method of computed tomography that comprises -
(1) Placement of a patient's body part opposite a multisensor digital X-ray receiver based on a set of optoelectronic converters having partially overlapped visual fields;
(2) X-ray transmission scanning of a selected patient’s body part within specified angular range by an X-ray emitter having a rectangular collimator;
(3) Conversion of X-ray radiation that had transmitted at various angles through the selected patient’s body part into visible light stream;
(4) Discrete detection of this light stream by many optoelectronic converters having characteristic working frequency, and conversion of obtained light beams into fragmentary analogous video signals,
(5) Conversion of said analogous video signals into fragmentary digital video signals;
(6) Correction of luminance and such geometrical defects of fragmentary digital video signals that caused by sizing and mounting errors of the optoelectronic converters and by partial overlapping visual fields of theirs;
(7) Conjunction of corrected fragmentary digital video signals into integral digital video signals appropriate to roentgenological images of oblique projections of patient’s body part; and
(8) Computer tomosynthesis on the basis of the roentgenological images series.
characterized in that
Said discrete detection of light stream and conversion of light beams into fragmentary analogous video signals execute by optoelectronic converters having working frequency no less than 250 fps;
Said fragmentary digital video signals record serially into a video buffer and delay in this video buffer till completion of said X-ray transmission scanning, and
Only then execute correction of luminance and geometrical defects of fragmentary digital video signals, conjunction of corrected fragmentary digital video signals into integral digital video signals and computer tomosynthesis.
2. The method according to the claim 1 characterized in that the X-ray transmission scanning of the selected patient’s body part within specified angular range realizes by linear movement and concomitant angular displacement of the rotary X-ray emitter having rectangular collimator along frontal surface of immobile X-ray receiver.
3. The method according to the claim 2, characterized in that said X-ray transmission scanning of the selected patient’s body part realizes within angular range ± 20°.
4. The method according to the claim 1 , characterized in that the X-ray transmission scanning of the selected patient’s body part within specified angular range realizes by synchronous angular movement of oppositely fixed said X-ray receiver and said X-ray emitter having the rectangular collimator.
5. The method according to the claim 4, characterized in that said X-ray transmission scanning of the selected patient’s body part realizes within angular range ± 110°.
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| UAA201813015 | 2018-12-28 | ||
| UAA201813015A UA125070C2 (en) | 2018-12-28 | 2018-12-28 | Method of computed tomography |
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